Hearing aid adapter

ABSTRACT

Presented herein are stand-alone hearing aid adapters configured to enable the use of the recipient&#39;s hearing aid to detect and process ambient sound signals and to convert output signals generated by the acoustic hearing aid into input signals useable by the implantable hearing prosthesis for generation and delivery of stimulation to a recipient.

BACKGROUND Field of the Invention

The present invention relates generally to hearing prostheses.

Related Art

Hearing loss, which may be due to many different causes, is generally oftwo types, conductive and/or sensorineural. Conductive hearing lossoccurs when the normal mechanical pathways of the outer and/or middleear are impeded, for example, by damage to the ossicular chain or earcanal. Sensorineural hearing loss occurs when there is damage to theinner ear, or to the nerve pathways from the inner ear to the brain.

Individuals who suffer from conductive hearing loss typically have someform of residual hearing because the hair cells in the cochlea areundamaged. As such, individuals suffering from conductive hearing losstypically receive an auditory prosthesis that generates motion of thecochlea fluid. Such auditory prostheses include, for example, acoustichearing aids, bone conduction devices, and direct acoustic stimulators.

In many people who are profoundly deaf, however, the reason for theirdeafness is sensorineural hearing loss. Those suffering from some formsof sensorineural hearing loss are unable to derive suitable benefit fromauditory prostheses that generate mechanical motion of the cochleafluid. Such individuals can benefit from implantable auditory prosthesesthat stimulate nerve cells of the recipient's auditory system in otherways (e.g., electrical, optical and the like). Cochlear implants areoften proposed when the sensorineural hearing loss is due to the absenceor destruction of the cochlea hair cells, which transduce acousticsignals into nerve impulses. An auditory brainstem stimulator is anothertype of stimulating auditory prosthesis that might also be proposed whena recipient experiences sensorineural hearing loss due to damage to theauditory nerve.

SUMMARY

In one aspect, a stand-alone hearing aid adapter is provided. Thestand-alone hearing aid adapter comprises: at least one input elementconfigured to receive hearing aid output signals from an acoustichearing aid; an adaption module configured to convert the hearing aidoutput signals into implantable hearing prosthesis input signals; and awireless transmitter configured to transmit the implantable hearingprosthesis input signals to an implantable hearing prosthesis.

In another aspect, a method is provided. The method comprises:receiving, at a hearing aid adapter in communication with an acoustichearing aid, hearing aid output signals generated by the acoustichearing aid based on detected sound signals; converting, with thehearing aid adapter, the hearing aid output signals into implantablehearing prosthesis input signals; and wirelessly transmitting theimplantable hearing prosthesis input signals from the hearing aidadapter to an implantable hearing prosthesis.

In another aspect, an implantable hearing prosthesis system is provided.The implantable hearing prosthesis system comprises: an implantablehearing prosthesis configured to be at least partially implanted in arecipient; and a stand-alone hearing aid adapter configured to becoupled with an acoustic hearing aid and to wirelessly stream processedsound signals from the acoustic hearing aid to the implantable hearingprosthesis.

BRIEF DESCRIPTION OF THE DRAWINGS

Embodiments of the present invention are described herein in conjunctionwith the accompanying drawings, in which:

FIG. 1 is a block diagram illustrating a hearing prosthesis system thatincludes a stand-alone hearing aid adapter in accordance withembodiments presented herein;

FIG. 2A is a block diagram of a stand-alone hearing aid adapter inaccordance with embodiments presented herein;

FIG. 2B is a block diagram of a cochlear implant configured to receivesignals from a stand-alone hearing aid adapter in accordance withembodiments presented herein;

FIG. 3 is a block diagram of a cochlear implant sound processorconfigured to process signals received from a stand-alone hearing aidadapter in accordance with embodiments presented herein;

FIG. 4 is a block diagram of another cochlear implant sound processorconfigured to process signals received from a stand-alone hearing aidadapter in accordance with embodiments presented herein;

FIG. 5 is a schematic diagram illustrating an arrangement for astand-alone hearing aid adapter in accordance with embodiments presentedherein;

FIG. 6 is a schematic diagram illustrating another arrangement for astand-alone hearing aid adapter in accordance with embodiments presentedherein;

FIG. 7 is a block diagram of a stand-alone hearing aid adapter inaccordance with embodiments presented herein; and

FIG. 8 is a flowchart of a method in accordance with embodimentspresented herein.

DETAILED DESCRIPTION

Individuals may suffer from different types and/or degrees of hearingloss, including conductive and/or sensorineural hearing loss. Thesedifferent types and/or degrees of hearing loss may be treated indifferent manners. For example, conductive hearing loss is commonlytreated with acoustic hearing aids that are designed to deliveramplified acoustic signals to a recipient's inner ear. In contrast,sensorineural hearing loss is generally treated using implantablehearing/auditory prostheses, such as cochlear implants, auditorybrainstem, etc., that directly stimulate nerve cells of the recipient'sauditory system.

In certain cases, an individual may experience changes in his/herhearing loss that results in the need to transition from a hearing aidtreatment regime (i.e., the use of an acoustic hearing aid) to animplantable treatment regime (i.e., use of an implantable hearingprosthesis). That is, certain recipients of acoustic hearing aids may,over time, be unable to continue to derive suitable benefit from theiracoustic hearing aid(s). In conventional techniques, these individualsare required to discard their familiar (and often expensive) acoustichearing aid, along with its accompanying user interface, accessories,remote controls, etc. and immediately adjust to use of a completeimplantable hearing prosthesis. However, implantable hearing prosthesescommonly include user interfaces that are different from those of therecipient's hearing aid, as well as often utilize different accessories,remote controls, etc. The requirement for a recipient to immediatelymake these adjustments not only makes the recipient's transition fromthe acoustic hearing aid to the implantable hearing prosthesisdifficult, but can also act as a financial or other impediment toinitiating the transition.

Hearing aid form factors and processors offer a wide set of processingoptions. Unfortunately, it is difficult to re-use hearing aid technologywithin an implantable system due to the prevalence of differentoperating platforms between hearing aids and implantable systems whichare often produced by different manufacturers. Accordingly, therecurrently exists no practical way to combine an acoustic hearing aidwith an implantable hearing prosthesis (such as a cochlear implant) foruse by a recipient to perceive sounds.

Presented herein are techniques and associated devices, referred toherein as stand-alone hearing aid adapters or simply hearing aidadapters, that are designed to enable a recipient to continue to usehis/her existing acoustic hearing aid even after receiving animplantable hearing prosthesis (e.g., when transitioning from a hearingaid solution to an implantable solution). In particular, the stand-alonehearing aid adapters presented herein are configured to enable the useof the recipient's hearing aid to detect and process ambient soundsignals. The stand-alone hearing aid adapters are also configured toconvert output signals generated by the acoustic hearing aid into inputsignals useable by the implantable hearing prosthesis for generation anddelivery of stimulation to the recipient's nerve cells. As a result, theimplantable hearing prosthesis receives signals that have been detectedby the sound input elements (e.g., microphones) of the acoustic hearingaid, and signals which have already undergone sound processing withinthe hearing aid.

For ease of illustration, embodiments are primarily described hereinwith reference to stand-alone hearing aid adapters for connecting anacoustic hearing aid with one specific type of implantable hearingprosthesis, namely a cochlear implant. However, it is to be appreciatedthat the stand-alone hearing aid adapters presented herein may be usedto connect hearing aids with other types of hearing prostheses, such asauditory brainstem stimulators.

FIG. 1 is block diagram of an exemplary hearing prosthesis system 100that includes a stand-alone hearing aid adapter 102 configured toretrofit an acoustic hearing aid 104 to provide input signals to acochlear implant 106. In particular, and as described further below, thestand-alone hearing aid adapter 102 is configured to replace an acousticreceiver of the acoustic hearing aid 104 such that hearing aid outputsignals 110 are resampled and converted into cochlear implant inputsignals 112. The stand-alone hearing aid adapter 102 is furtherconfigured to provide the cochlear implant input signals 112 to thecochlear implant 106. As described further below, the cochlear implantinput signals 112 may, in certain embodiments, be wirelessly transmittedto an external or implanted component of the cochlear implant 106.

FIG. 2A is a block diagram illustrating one arrangement for astand-alone hearing aid adapter in accordance with embodiments presentedherein, which is shown in FIG. 2 as stand-alone hearing aid adapter 202.For completeness, FIG. 2A also illustrates an example arrangement for aconventional acoustic hearing aid 206. FIG. 2B illustrates an examplearrangement for a cochlear implant 206 that may operate with thestand-alone hearing aid adapter 202 of FIG. 2A.

Referring first to the acoustic hearing aid 204, shown are two soundinput elements in the form of microphones 214(A) and 214(B), ananalog-to-digital (A/D) converter 216, a hearing aid sound processor218, a digital-to-analog (D/A) converter 220, an amplifier 220, anacoustic receiver connector 224, and one or more batteries 223. The oneor more batteries 223, which may be a disposable or rechargeablebatteries, are configured to supply power to the other elements of theacoustic hearing aid 204.

The microphones 214(A) and 214(B) are configured to detect ambient soundsignals 211 and to generate electrical signals therefrom. It is to beappreciated that, in addition to the two microphones 214(A) and 214(B),acoustic hearing aids may also include other sound input elements, suchas telecoils, audio input ports, etc. However, merely for ease ofillustration, these other types of sound input elements have beenomitted from FIG. 2A.

Returning to the example arrangement of FIG. 2A, the electrical signalsgenerated by the microphones 214(A) and 214(B) are provided to the A/Dconverter 216 which converts the electrical signals generated by themicrophones 214(A) and 214(B) from the analog domain to the digitaldomain. The A/D converter 216 provides the resulting digital signals toa hearing aid sound processor 218.

The hearing aid sound processor 218 is, for example, a digital signalprocessor (DSP) that is generally configured to process and refine thedigital signals before conversion back into an acoustic sound. Forexample, the hearing aid sound processor 218 may be configured toperform noise reduction/speech enhancement (e.g., execute adaptivealgorithms, emphasize sounds of particular frequency, etc.), executeanti-feedback control mechanisms, perform automatic switching betweendifferent listening programs, among other operations. However,regardless of the specific operations performed, the hearing aid soundprocessor 218 outputs digital signals that are processed (e.g.,enhanced) versions of the ambient sound signals detected by themicrophones 214(A) and 214(B) (i.e., generates processed sound signals).

The processed sound signals generated by the hearing aid sound processor218 are provided to a D/A converter 220 that converts the processedsound signals from the digital domain to the analog domain. An amplifier222 amplifies the processed analog signals to generate amplifiedprocessed sound signals, which are then provided to an acoustic receiverconnector (receiver connector) 224. The receiver connector 224 is anelement that enables an acoustic receiver (e.g., speaker) to bedetachably electrically connected thereto to the elements of theacoustic hearing aid 204. In certain examples, the receiver connector224 is a single or multi-pin/wire port, receptacle, socket, or otherfemale connector portion that is configured to mate with a correspondingmale connector portion, such a single or multi-pin/wire plug, jack, pin,etc., of an acoustic receiver. In other examples, the receiver connector224 is a male connector portion that is configured to mate with acorresponding female connector portion of an acoustic receiver.

In a number of conventional acoustic hearing aids, the receiverconnector 224 represents the exit point for processed (and amplified)signals generated by the acoustic hearing aid 204 within the electricdomain As such, the signals provided to the receiver connector 224 aresometimes referred to herein as hearing aid electric output signals.

However, as shown in FIG. 2A, no acoustic receiver is connected to thereceiver connector 224. Instead, the stand-alone hearing aid adapter 202is connected to the acoustic hearing aid 204 via the receiver connector224. More specifically, the stand-alone hearing aid adapter 202comprises an adapter connector 226 that has an arrangement so as tomechanically and electrically mate with the receiver connector 224. Assuch, the stand-alone hearing aid adapter 202 receives the hearing aidoutput signals (i.e., the processed analog signals generated by theacoustic hearing aid 204).

As noted above, the receiver connector 224 may have differentarrangements (e.g., comprise a male or female connector portion). Assuch, an adapter connector 226 in accordance with embodiments presentedherein may also have different arrangements so as to properly mate withthe receiver connector 224.

The stand-alone hearing aid adapter 202 includes an adaption module 215that is configured to convert the hearing aid electric output signalsinto input signals useable by the cochlear implant 206 (shown in FIG.2A), sometimes referred to herein as implantable hearing prosthesisinput signals. In the embodiment of FIG. 2A, the adaption module 215comprises an A/D converter 228 and an audio encoder 230. The A/Dconverter 228 is configured to convert the hearing aid electric outputsignals from the analog domain to the digital domain. The audio encoder230 is configured to compress the digital signals received from the A/Dconverter 228 (e.g., according to a given audio file format or streamingaudio format). That is, in general, the audio encoder 230 executes analgorithm configured to represent the digital audio signal with aminimum number of bits while retaining the quality of the audio. In oneform, the A/D converter 228 and the audio encoder 230 collectively forman audio codec.

The audio encoder 230 generates a compressed audio signal that isprovided to a wireless transmitter or transceiver 232. The wirelesstransmitter 232 is configured to wirelessly transmit the compressedaudio signals to the cochlear implant 206. In certain, embodiments thewireless transmitter 232 is a Bluetooth® or Bluetooth® Low Energy (BLE)transmitter that communicates using short-wavelength Ultra HighFrequency (UHF) radio waves in the industrial, scientific and medical(ISM) band from 2.4 to 2.485 gigahertz (GHz). Bluetooth® is a registeredtrademark owned by the Bluetooth® SIG. However, it is to be appreciatedthat other types of wireless transmission may be used in alternativeembodiments.

As noted above, the compressed audio signals represent a processed(enhanced) digital version of the sound signals received by the soundinput elements (e.g., microphones 214(A) and 214(B)) of the acoustichearing aid 204. In addition, as described further below, the compressedaudio signals are useable by the cochlear implant 206 for generation anddelivery of stimulation signals to a recipient. As such, the compressedaudio signals are sometimes referred to herein as implantable hearingprosthesis input signals and are represented in FIGS. 2A and 2B by arrow212.

As noted, FIG. 2B illustrates an example arrangement for a cochlearimplant 206 that may operate with the stand-alone hearing aid adapter202 of FIG. 2A. The cochlear implant 206 of FIG. 2B includes an externalcomponent 242 and an internal/implantable component 244, although otherarrangements may have a totally-implantable configuration. The externalcomponent 242 is configured to be directly or indirectly attached to thebody of a recipient, while the implantable component 244 is configuredto be subcutaneously implanted within the recipient (i.e., under theskin/tissue 201 of the recipient).

Traditionally, external components of a cochlear implant have beenformed by two elements, a behind-the-ear unit and a separate coil unit,which are connected by a cable. In these traditional arrangements, anysound input elements, sound processing elements, power sources, etc. arehoused in a behind-the-ear component, while the separate coil unitincludes a radio-frequency (RF) coil for use in transcutaneouscommunication with the implantable component. However, in the example ofFIG. 2B, the external component 242 is a so-called “button” unit wherethe sound processing elements, power source, external coil, etc. areintegrated into a single housing. As noted below, the button unit 242also includes a magnet and is configured to be worn at a location wherethis magnet can be magnetically coupled to an implantable magnet.Although FIG. 2B illustrates the external component 242 as a buttonunit, it is to be appreciated that the external component 242 may haveother arrangements.

The button unit 242 comprises a wireless receiver or transceiver 246, anaudio decoder 248, a cochlear implant processor 250, an external coil252, a battery 256, and a magnet (not shown in FIG. 2B) fixed relativeto the external coil 252. The wireless receiver 246 is configured forcommunication with the wireless transmitter 232 (FIG. 2A) in thestand-alone hearing aid adapter 202 so as to wirelessly receive theimplantable hearing prosthesis input signals 212. The audio decoder 248is configured to decompress the implantable hearing prosthesis inputsignals 212 (e.g., according to a given audio file format or streamingaudio format). That is, in general, the audio decoder 248 executes analgorithm to reverse the compression performed by the audio encoder 230in the stand-alone hearing aid adapter 202. The decompressed signals arethen provided to the cochlear implant processor 250. The encoded outputsignals representative of electrical stimulation, which are representedin FIG. 2B by arrow 258, are transmitted to the implantable component244 via a closely coupled radio frequency (RF) link (e.g., a 5 megahertz(MHz) inductive RF link).

As described further below, the cochlear implant processor 250 executesone or more operations to convert the decompressed signals received fromthe audio decoder 248 into encoded output signals that representelectric (current) stimulation for delivery to the recipient. Also asdescribed below, the number and types of operations performed by thecochlear implant processor 250 may vary in different embodiments, butgenerally include sound coding operations. In certain embodiments, thecochlear implant processor 250 may execute sound processing operations.

As shown in FIG. 2B, the implantable component 244 comprises an implantbody (main module) 262, a lead region 264, and an elongateintra-cochlear stimulating assembly 266. The implant body 262 generallycomprises a hermetically-sealed housing 268 in which an internal RFtransceiver unit (transceiver) 270 and a stimulator unit 272 aredisposed. The implant body 262 also includes an internal/implantablecoil 274 that is generally external to the housing 268, but which isconnected to the RF transceiver 270 via a hermetic feedthrough (notshown in FIG. 2B). Implantable coil 274 is typically a wire antenna coilcomprised of multiple turns of electrically insulated single-strand ormulti-strand platinum or gold wire. The electrical insulation ofimplantable coil 274 is provided by a flexible molding (e.g., siliconemolding), which is not shown in FIG. 2B. Generally, a magnet is fixedrelative to the implantable coil 274 for magnetic coupling with themagnet in the button sound processing unit 242.

Elongate stimulating assembly 266 is configured to be at least partiallyimplanted in the recipient's cochlea (not shown) and includes aplurality of longitudinally spaced intra-cochlear electrical stimulatingcontacts (electrodes) 276 that collectively form a contact array 278 fordelivery of electrical stimulation (current) to the recipient's cochlea.Stimulating assembly 266 extends through an opening in the cochlea(e.g., cochleostomy, the round window, etc.) and has a proximal endconnected to stimulator unit 272 via lead region 264 and a hermeticfeedthrough (not shown in FIG. 2B). Lead region 264 includes a pluralityof conductors (wires) that electrically couple the electrodes 276 to thestimulator unit 272.

As noted, the output signals 258 are sent to the implantable component244 via a closely-coupled RF link formed by the external coil 252 andthe implantable coil 274. More specifically, the magnets fixed relativeto the external coil 252 and the implantable coil 274 facilitate theoperational alignment of the external coil 252 with the implantable coil274. This operational alignment of the coils enables the external coil252 to transmit the encoded data signals 258, as well as power signalsreceived from battery 256, to the implantable coil 274.

In general, the encoded data signals 258 are received at the RFtransceiver 270 where they are converted into output signals for thestimulator unit 272. The stimulator unit 272 is configured to utilizethe output signals received from the RF transceiver 270 to generateelectrical stimulation signals (e.g., current signals) for delivery tothe recipient's cochlea via one or more stimulating contacts 276. Inthis way, cochlear implant 206 electrically stimulates the recipient'sauditory nerve cells, bypassing absent or defective hair cells thatnormally transduce acoustic vibrations into neural activity, in a mannerthat causes the recipient to perceive one or more components of thereceived sound signals.

As noted, FIG. 2B illustrates a cochlear implant having both externaland implantable components. However, it is to be appreciated thatembodiments presented herein may include totally implantable cochlearimplants where all components of the cochlear implant are configured tobe implanted under the skin/tissue of a recipient. In these embodiments,the elements shown as part of the button unit in FIG. 2B, including thewireless receiver, audio decoder, cochlear implant processor, andbattery would be included in the implantable component. Because allcomponents of totally implant cochlear implant are implantable, suchcochlear implants operate, for at least a finite period of time, withoutthe need of an external device.

As detailed above, in the arrangements of FIGS. 2A and 2B, as well inarrangements that make use of a totally implantable cochlear implant,the sound signals that are used by the cochlear implant 206 to generatethe electrical stimulation signals for delivery to the recipient arefirst detected by the acoustic hearing aid 204. The acoustic hearing aid204 performs hearing aid processing operations on these received soundsignals and the processed sound signals are then sent to the cochlearimplant 206 via the stand-alone adapter 202. In other words, inaccordance with the above embodiments, the stand-alone hearing aidadapter 202 converts the conventional acoustic hearing aid 204 into astreaming ambient sound/audio source for the cochlear implant 206.Stated differently, the stand-alone hearing aid adapter 202 wirelesslystreams an enhanced version of ambient sounds from the hearing aid tothe cochlear implant 206, thereby allowing the recipient to continue touse his/her acoustic hearing aid, including the controls, programs, etc.associated with the hearing aid, even after he/she receives the cochlearimplant 206.

As noted above, hearing aid adapters in accordance with the embodimentspresented herein are “stand-alone” adapters, meaning that the adaptersoperate independent from both the acoustic hearing aid and the cochlearimplant that are linked by the adapter. For example, the stand-alonehearing aid adapter 202 includes one or more internal batteries (e.g.,replaceable or rechargeable batteries) 234 so that it does not need todraw power from either the acoustic hearing aid or the cochlear implant.In addition, the hearing aid adapters in accordance with the embodimentspresented herein are not required to be aware of the specific processingor other operations performed at either the acoustic hearing aid or thecochlear implant.

Similarly, the acoustic hearing aid and, in certain examples, thecochlear implant, need not be aware of the presence or use of thehearing aid adapter. In particular, the acoustic hearing aid merelyperforms its standard operations to output a signal to its receiverconnector, and the acoustic hearing has no knowledge of subsequentoperations. Moreover, from the perspective of the cochlear implant, thesignal received from the stand-alone adapter can be interpreted as astreaming audio source.

Due to the stand-alone nature of the hearing aid adapters presentedherein, the adapters can operate with hearing aids and cochlear implantsof different makes (i.e., different manufacturers) and models, includingenabling the interoperation of acoustic hearing aids and cochlearimplants from different manufacturers. As a result of the ability tooperate with, and enable interoperation by, different makes/models ofhearing aids and cochlear implants, the stand-alone hearing aid adapterspresented herein are sometimes referred to as “universal” hearing-aidadapters.

The stand-alone/universal nature of the hearing aid adapters presentedherein may have several advantages. For example, not only do thestand-alone hearing aid adapters presented herein enable a recipient tocontinue using his/her acoustic hearing aid and accessories whenupgrading to a cochlear implant, but the adapters presented herein mayalso enable implantable hearing prosthesis manufactures to rapidlyleverage hearing aid technology when delivering new products as well asdevelop lower cost implantable solutions.

FIG. 3 is a block diagram illustrating details of a cochlear implantprocessor 350 that, in certain examples, can function as the cochlearimplant processor 250 of FIG. 2B. More particularly, the cochlearimplant processor 350 may utilize signals 380 received from astand-alone hearing aid adapter in accordance with embodiments presentedherein. As shown, the cochlear processor 350 comprises a pre-filterbankprocessing module 382, a filterbank 384, a post-filterbank processingmodule 386, a channel selection module 388, and a channel mapping module390. The pre-filterbank processing module 382 receives the signals 380sent from a stand-alone adapter via a wireless receiver and decoder (notshown in FIG. 3) and is configured to, as needed, prepare those signalsfor subsequent processing. The pre-filterbank processing module 382generally includes broadband automatic gain control and frequencyshaping and generates a pre-filtered input signal 383 that is providedto the filterbank 384.

The filterbank 384 uses the pre-filtered input signal 383 to generate asuitable set of bandwidth limited channels, or frequency bins, that eachincludes a spectral component of the received sound signals that are tobe utilized for subsequent sound processing. That is, the filterbank 384is a plurality of band-pass filters that separates the pre-filteredinput signal 383 into multiple components, each one carrying a singlefrequency sub-band of the original signal (i.e., frequency components ofthe received sounds signal as included in pre-filtered input signal383).

The channels created by the filterbank 384 are sometimes referred toherein as processing channels, and the sound signal components withineach of the processing channels are sometimes referred to herein in asband-pass filtered signals or channelized signals. As described furtherbelow, the band-pass filtered or channelized signals created by thefilterbank 384 may be adjusted/modified as they pass through theprocessing path. As such, the band-pass filtered or channelized signalsare referred to differently at different stages of the processing path.However, it will be appreciated that reference herein to a band-passfiltered signal or a channelized signal may refer to the spectralcomponent of the received sound signals at any point within theprocessing path (e.g., pre-processed, processed, selected, etc.).

At the output of the filterbank 384, the channelized signals areinitially referred to herein as pre-processed signals 385. The number‘m’ of channels and pre-processed signals 385 generated by thefilterbank 384 may depend on a number of different factors including,but not limited to, implant design, number of active electrodes, codingstrategy, and/or recipient preference(s). In certain arrangements,twenty-two (22) channelized signals are created and the cochlear implantprocessor 350 is said to include 22 channels.

In the example of FIG. 3, the cochlear implant processor 350 alsoincludes a post-filterbank processing module 386. The post-filterbankprocessing module 386 is configured to perform a number of soundprocessing operations on the pre-processed signals 385. These soundprocessing operations may include, for example gain adjustments (e.g.,multichannel gain control), noise reduction operations, signalenhancement operations (e.g., speech enhancement), etc., in one or moreof the channels. As used herein, noise reduction is refers to processingoperations that identify the “noise” (i.e., the “unwanted”) componentsof a signal, and then subsequently reduce the presence of these noisecomponents. Signal enhancement refers to processing operations thatidentify the “target” signals (e.g., speech, music, etc.) and thensubsequently increase the presence of these target signal components.Speech enhancement is a particular type of signal enhancement. Afterperforming the sound processing operations, the post-filterbankprocessing module 386 outputs a plurality of processed channelizedsignals 387.

In the embodiment of FIG. 3, the channel selection module 388 selects asubset ‘n’ of the ‘m’ processed channelized signals 387 for use ingeneration of stimulation for delivery to a recipient (i.e., the soundprocessing channels are reduced from ‘m’ channels to ‘n’ channels). Inone specific example, the ‘n’ largest amplitude channels (maxima) fromthe ‘m’ available combined channel signals/masker signals is made, with‘m’ and ‘n’ being programmable during cochlear implant fitting, and/oroperation of the cochlear implant. It is to be appreciated thatdifferent channel selection methods could be used, and are not limitedto maxima selection. The signals selected at channel selection module388 are represented in FIG. 3 by arrows 389 and are referred to asselected channelized signals or, more simply, selected signals.

The cochlear implant processor 350 also comprises the channel mappingmodule 390. The channel mapping module 390 is configured to map theamplitudes of the selected signals 389 into a set of stimulationcommands that represent the attributes of stimulation signals (currentsignals) that are to be delivered to the recipient so as to evokeperception of the received sound signals. This channel mapping mayinclude, for example, threshold and comfort level mapping, dynamic rangeadjustments (e.g., compression), volume adjustments, etc., and mayencompass sequential and/or simultaneous stimulation paradigms.

In the embodiment of FIG. 3, the set of stimulation commands thatrepresent the stimulation signals are encoded for transcutaneoustransmission (e.g., via an RF link) to an implantable component (notshown). This encoding is performed, in the specific example of FIG. 3,at channel mapping module 390. As such, channel mapping module 390 issometimes referred to herein as a channel mapping and encoding moduleand operates as an output block configured to convert the plurality ofchannelized signals into a plurality of output signals 391. The outputsignals 391 comprise a plurality of encoded signals for delivery to theimplantable component via an RF coil.

FIG. 3 illustrates a cochlear implant processor that implements acomplete or full sound processing path that is operable to convert soundsignals received from a stand-alone adapter, as well as signals fromother sound sources (e.g., microphones), into encoded output signals.That is, cochlear implant processor 350 of FIG. 3 may be referred to asa “sound processor” because it performs sound processing operations(i.e., the operations of the post-filterbank processing module 386). Incontrast, FIG. 4 is a block diagram illustrating details of a simplifiedcochlear implant processor 450 that, in certain examples, can functionas the cochlear implant processor 250 of FIG. 2B. In the example of FIG.4, the cochlear implant processor 450 does not perform sound processingoperations and represents a processor that is specifically designed toprocess signals 380 received from a stand-alone hearing aid adapter inaccordance with embodiments presented herein.

More specifically as shown, the cochlear implant processor 450 comprisesa filterbank 384, a channel selection module 388, and a channel mappingmodule 390, that each operate similar to the filterbank, channelselection module, and mapping and encoding module, respectively,described above with reference to FIG. 3. However, as shown, thepre-filterbank processing module 382 and the post-filterbank processingmodule 386 present in the cochlear implant processor 350 (FIG. 3) arenot present in cochlear implant processor 450. The cochlear implantprocessor 450 does not include a pre-filterbank processing module or apost-filterbank processing module because these operations are performedby the acoustic hearing aid processor. In other words, since the soundprocessor 450 operates only on signals received from a stand-alonehearing aid adapter, the pre-filterbank processing and post-filterbankprocessing operations are redundant to the operations performed by theacoustic hearing aid and, as such, are not needed.

In certain embodiments, the arrangement of FIG. 4 may be implemented asa static configuration within a cochlear implant. That is, the cochlearimplant is specifically configured to operate exclusively with (on)signals received from a stand-alone hearing aid adapter (i.e., signalsstreamed from an acoustic hearing aid).

In other embodiments, the arrangement of FIG. 4 may be implemented as aspecific operational mode (i.e., a “simplified mode”) of a full-featuredcochlear implant processor (e.g., as a specialized mode of a cochlearimplant processor that has all of the functionality shown in FIG. 3). Inother words, the arrangement of FIG. 4 could be implemented by thecochlear implant processor 350 of FIG. 3 by configuring the cochlearimplant processor 350 to skip, eliminate, or otherwise bypass thepre-filterbank processing and post-filterbank processing operations. Inthese embodiments, the cochlear implant processor 350 could be locked tooperate in the simplified mode (e.g., by a user) and then switched to afull-featured mode the acoustic hearing aid (and adapter) are no longerused. Alternatively, the cochlear implant processor 350 could beconfigured to dynamically switch between the simplified mode when thecochlear implant processor 350 detects signals received from a hearingaid adapter (i.e., signals received at a wireless receiver) and afull-featured mode when signals are received from other sound sources.

Stand-alone hearing aid adapters in accordance with embodiments of thepresent invention may have a number of different physical arrangementsfor use with an acoustic hearing aid. For example, FIG. 5 illustrates astand-alone hearing aid adapter 502 having a housing 503 formed as anearhook attachment for a behind-the-ear (BTE) acoustic hearing aid 504.Located within the housing 503 are the functional components of thestand-alone hearing aid adapter 502 (e.g., A/D converter, audio encoder,wireless transmitter, battery, etc.).

In this arrangement of FIG. 5, the stand-alone hearing aid adapter 502is configured to both electrically and physically mate with the BTEacoustic hearing aid 504 via the receiver connector of the hearing aid(not shown in FIG. 5). The physical connection/mating between thestand-alone hearing aid adapter 502 and the BTE acoustic hearing aid 504is substantially rigid such that the-alone hearing aid adapter assistsin retaining the hearing aid on the recipient's ear (i.e., rests on therecipient's outer ear).

FIG. 6 illustrates a stand-alone hearing aid adapter 602 that isconfigured as an in-the-ear (ITE) component. In this arrangement of FIG.6, the stand-alone hearing aid adapter 602 comprises a housing 603 thathas a shape so as to be inserted and retained into the recipient's outerear. Located within the housing 603 are the functional components of thestand-alone hearing aid adapter 602 (e.g., A/D converter, audio encoder,wireless transmitter, battery, etc.). The stand-alone hearing aidadapter 602 also includes a wire 605 that extends from the housing 603to an adapter connector 626 that is configured to mechanically andelectrically interface with a receiver connector 624 in an acoustichearing aid 604. In other words, in the arrangement of FIG. 6, thefunctional components of the stand-alone hearing aid adapter 602 arelocated within the recipient's outer ear and are electrically connectedto the acoustic hearing aid 604 that is, for example, a BTE hearing aidworn on the recipient's outer ear.

As noted above, stand-alone hearing aid adapters in accordance withembodiments presented herein may have a number of different physicalarrangements that are useable to enable interoperation of an acoustichearing aid with a cochlear implant or other implantable hearingprosthesis. As such, it is to be appreciated that the arrangements shownin FIGS. 5 and 6 are illustrative.

The stand-alone hearing adapters in accordance with embodimentspresented herein have primarily described above with reference to aphysical electrical connection between the hearing aid and the adapter,where the adapter connects at the location of a detachable acousticreceiver (i.e., the adapter replaces the acoustic receiver). In certainembodiments presented herein, stand-alone hearing aid adapters may beconfigured to use an acoustic coupling, rather than an electriccoupling, with a hearing aid. One such example arrangement is shown inFIG. 7 as stand-alone hearing aid adapter 702. For completeness, FIG. 7also illustrates an example arrangement for a conventional acoustichearing aid 704 that may operate with the stand-alone hearing aidadapter 702.

Referring first to the acoustic hearing aid 704, shown are two soundinput elements in the form microphones 714(A) and 714(B), an A/Dconverter 716, a hearing aid sound processor 718, a D/A converter 720,an amplifier 722, a battery 723, and an acoustic receiver 725. As noted,the acoustic hearing aids may also include other sound input elements,such as telecoils, audio input ports, etc. which, for ease ofillustration, have been omitted from FIG. 7.

The microphones 714(A) and 714(B) are configured to detect ambient soundsignals 711 and to generate electrical signals therefrom. The electricalsignals generated by the microphones 714(A) and 714(B) are provided tothe A/D converter 716 for conversion from the analog domain to thedigital domain. The resulting digital signals are then provided to thehearing aid sound processor 718. The hearing aid sound processor 718 is,for example, a digital signal processor (DSP) that is generallyconfigured to process and refine the digital signals before conversionback into an acoustic sound. The hearing aid sound processor 718 outputsdigital signals that are processed (e.g., enhanced) versions of thesound signals received by the microphones 714(A) and 714(B) (i.e.,processed sound signals).

The processed sound signals generated by the hearing aid sound processor718 are provided to the D/A converter 720 for conversion from thedigital domain to the analog domain. The amplifier 722 amplifies theprocessed analog signals to generate amplified signals, which are thenprovided to the acoustic receiver (e.g., speaker) 725. The acousticreceiver 725 uses the amplified signals to generate acoustic soundsignals 727 that represent a processed/enhanced and amplified version ofthe sound signals 711 originally received by the microphones 714(A) and714(B). The acoustic sound signals 727 are sometimes referred to hereinas hearing aid acoustic output signals.

As shown in FIG. 7, the stand-alone hearing aid adapter 702 includes oneor more microphones 729 that are configured to resample the hearing aidacoustic output signals 727 generated by the acoustic receiver 725. Thatis, the one or more microphones 729 receive the hearing aid acousticoutput signals 727 via an acoustic coupling with the hearing aid 704.The one or more microphones 729 are configured to generate electricalsignals based on the hearing aid acoustic output signals 727.

The stand-alone hearing aid adapter 702 includes an adaption module 715that is configured to convert the hearing aid acoustic output signals727 into input signals useable by a cochlear implant (not shown in FIG.7). In the embodiment of FIG. 7, the adaption module 715 comprises anA/D converter 728 that is configured to convert the electrical signalsgenerated by the one or more microphones 729 from the analog domain tothe digital domain. The adaption module 715 also comprises an audioencoder 730 that is configured to compress the digital signals receivedfrom the A/D converter 728. That is, in general, the audio encoder 730executes an algorithm configured to represent digital audio signal witha minimum number of bits while retaining the quality of the audio. Inone form, the A/D converter 728 and the audio encoder 730 collectivelyform an audio codec.

The audio encoder 730 generates a compressed audio signal that isprovided to a wireless transmitter 732. The wireless transmitter 732 isconfigured to wirelessly transmit the compressed audio signals to thecochlear implant 706. In certain, embodiments the wireless transmitter732 is a Bluetooth® or BLE transmitter that communicates usingshort-wavelength UHF radio waves in the ISM band from 2.4 to 2.485 GHz.Bluetooth® is a registered trademark owned by the Bluetooth® SIG.However, it is to be appreciated that other types of wirelesstransmission may be used in alternative embodiments.

As noted above, the compressed audio signals represent a processed(enhanced) version of the sound signals received by the sound inputelements (e.g., microphones 714(A) and 714(B)) of the acoustic hearingaid 704. In addition, the compressed audio signals are useable by thecochlear implant for generation and delivery of stimulation signals to arecipient. As such, the compressed audio signals are sometimes referredto herein as cochlear implant input signals, and are represented in FIG.7 by arrow 712.

The use of a stand-alone hearing aid adapter in accordance withembodiments present herein may also enable a simplified cochlear implantfitting procedure where a maximum comfort level (C level) could set, forexample, with a single Master Volume type control, and the fine tuningcould then be handled by the hearing fitting software, includingmeasuring hearing thresholds (T levels), etc. More specifically, inaccordance with embodiments presented herein, once a C-Level is set forthe cochlear implant sound processor, further audiological programmingcould exclusively focus on the hearing aid, and be performed by anaudiologist only familiar with hearing aid technology. For example, ifthe recipient is having difficulty hearing soft-sounds, then the gain atlow sound-pressure levels could be increased in the hearing aidprogramming software by the audiologist and applied to the hearing aid.This would flow through to the cochlear implant without creating anydiscomfort since the C-Levels are untouched, resolving the problem. Thissort of approach is only relevant when the cochlear implant is used withthe hearing aid as the front-end system, which is enabled by thestand-alone adapter.

This approach can be extended to follow a complete hearing aidprogramming methodology whereby the hearing thresholds are firstmeasured at a set of frequencies, resulting in the recipient'saudiogram. This audiogram is then used to prescribe hearing aid gainswhich can be further adjusted by the audiologist based on their clinicalpractice and are ultimately programmed into the device. In this mode,the cochlear implant sound processor is initially set up with therecipient's C-levels which is just setting the upper bound ofcomfortable stimulation. In one example, the recipient can complete thisstep themselves using a Master Volume control on a remote control,mobile phone, etc. In these examples, the device also be ‘by default’configured with very low T-levels which would typically be below thetrue threshold of hearing perceived by the recipient. The hearingthresholds are instead measured within the hearing-aid software suiteand methodology.

FIG. 8 is a flowchart of a method 892 in accordance with embodimentspresented herein. Method 892 begins at 894 where a hearing aid adapterin communication with an acoustic hearing aid receives hearing aidoutput signals generated by the acoustic hearing aid based on detectedsound signals. At 896, the hearing aid adapter converts the hearing aidoutput signals into implantable hearing prosthesis input signals. At898, the implantable hearing prosthesis input signals are wirelesslytransmitted from the hearing aid adapter to an implantable hearingprosthesis.

In certain arrangements, a stand-alone hearing aid adapter enables arecipient to continue use of a hearing aid when transitioning to animplantable hearing prosthesis, such as a cochlear implant. The abilityto continue use of the hearing aid has several advantages, includingreduction in financial burden, elimination of the need to learn newcontrols or purchase new accessories, simplified fitting, etc. Oneadditional benefit of a stand-alone hearing aid adapter in accordancewith embodiments presented herein is the ability to enable bilateralcommunications with a contra-lateral prosthesis. Continued bilateralcommunications is difficult without the stand-alone hearing aid adapteras it is unlikely that a standard acoustic hearing aid would be able towirelessly communicate with a standard cochlear implant processor.

It is to be appreciated that the embodiments presented herein are notmutually exclusive.

The invention described and claimed herein is not to be limited in scopeby the specific preferred embodiments herein disclosed, since theseembodiments are intended as illustrations, and not limitations, ofseveral aspects of the invention. Any equivalent embodiments areintended to be within the scope of this invention. Indeed, variousmodifications of the invention in addition to those shown and describedherein will become apparent to those skilled in the art from theforegoing description. Such modifications are also intended to fallwithin the scope of the appended claims.

What is claimed is:
 1. A stand-alone hearing aid adapter, comprising: atleast one input element configured to receive hearing aid output signalsfrom an acoustic hearing aid; an adaption module configured to convertthe hearing aid output signals into implantable hearing prosthesis inputsignal, wherein the adaption module comprises an analog-to-digitalconverter and an audio encoder; and a wireless transmitter configured totransmit the implantable hearing prosthesis input signals to animplantable hearing prosthesis.
 2. The stand-alone hearing aid adapterof claim 1, wherein the hearing aid output signals are electricalsignals, and wherein the at least one input element is an electricalconnector configured to mate with an acoustic receiver connector of theacoustic hearing aid.
 3. The stand-alone hearing aid adapter of claim 1,wherein the hearing aid output signals are acoustic signals transmittedby an acoustic receiver, and wherein the at least one input element is amicrophone configured to sample the acoustic signals.
 4. The stand-alonehearing aid adapter of claim 1, further comprising a housing forming anearhook that is configured for attachment to an outer ear of arecipient, wherein the adaption module and the wireless transmitter arelocated in the housing.
 5. The stand-alone hearing aid adapter of claim1, further comprising an in-the-ear housing configured to be insertedinto an outer ear of a recipient, wherein the adaption module and thewireless transmitter are located in the in-the-ear housing.
 6. Thestand-alone hearing aid adapter of claim 1, further comprising abattery.
 7. A method, comprising: receiving, at a hearing aid adapter incommunication with an acoustic hearing aid, analog hearing aid outputsignals generated by the acoustic hearing aid based on detected soundsignals; converting, with an analog-to-digital converter in the hearingaid adapter, the analog hearing aid output signals into digital signals;encoding, with an audio encoder in the hearing aid adapter, the digitalsignals into implantable hearing prosthesis input signals; andwirelessly transmitting the implantable hearing prosthesis input signalsfrom the hearing aid adapter to an implantable hearing prosthesis. 8.The method of claim 7, further comprising: wirelessly receiving theimplantable hearing prosthesis input signals at the implantable hearingprosthesis; and converting the implantable hearing prosthesis inputsignals into stimulation signals to evoke perception of the detectedsound signals when delivered to a recipient of the implantable hearingprosthesis.
 9. The method of claim 8, wherein the converting theimplantable hearing prosthesis input signals into stimulation signals isperformed without sound processing operations.
 10. The method of claim7, further comprising: detecting the sound signals at an acoustichearing aid; and performing sound processing at the acoustic hearing aidto convert the detected sound signals into the hearing aid outputsignals.
 11. The method of claim 7, wherein receiving the hearing aidoutput signals comprises: receiving electrical signals via an electricalconnector configured to mate with an acoustic receiver connector of theacoustic hearing aid.
 12. The method of claim 7, wherein receiving thehearing aid output signals at the hearing aid adapter comprises:receiving, via at least one input element, acoustic signals transmittedby an acoustic receiver, and wherein the at least one input element is amicrophone configured to sample the acoustic signals.
 13. An implantablehearing prosthesis system, comprising: an implantable hearing prosthesisconfigured to be at least partially implanted in a recipient; and astand-alone hearing aid adapter configured to be coupled with anacoustic hearing aid and to wirelessly stream processed sound signalsfrom the acoustic hearing aid to the implantable hearing prosthesis,wherein the stand-alone hearing aid adapter comprises ananalog-to-digital converter and an audio encoder.
 14. The implantablehearing prosthesis system of claim 13, wherein the stand-alone hearingaid adapter is electrically coupled to the acoustic hearing aid, andwherein the processed sound signals are received by the stand-alonehearing aid adapter as electrical signals.
 15. The implantable hearingprosthesis system of claim 13, wherein the stand-alone hearing aidadapter is acoustically coupled to the acoustic hearing aid, and whereinthe processed sound signals are received by the stand-alone hearing aidadapter as acoustic signals.
 16. The implantable hearing prosthesissystem of claim 13, wherein the stand-alone hearing aid adaptercomprises: a housing forming an earhook that is configured forattachment to an outer ear of a recipient of the implantable hearingprosthesis, wherein a wireless transmitter is located in the housing forcommunication with a wireless receiver in the implantable hearingprosthesis.
 17. The implantable hearing prosthesis system of claim 13,wherein the stand-alone hearing aid adapter comprises: an in-the-earhousing configured to be positioned in an outer ear of a recipient ofthe implantable hearing prosthesis, wherein a wireless transmitter islocated in the in-the-ear housing for communication with a wirelessreceiver in the implantable hearing prosthesis, and wherein theanalog-to-digital converter, audio encoder, and the wireless transmitterare located in the in-the-ear housing.
 18. The implantable hearingprosthesis system of claim 13, wherein the implantable hearingprosthesis is configured to: wirelessly receive the processed soundsignals from the stand-alone hearing aid adapter; and convert theprocessed sound signals into stimulation signals for delivery to arecipient of the implantable hearing prosthesis.
 19. The implantablehearing prosthesis system of claim 13, wherein the implantable hearingprosthesis is a cochlear implant.
 20. The implantable hearing prosthesissystem of claim 19, wherein the implantable hearing prosthesis is atotally implantable cochlear implant having an implantable wirelessreceiver.